Methods and systems for X-ray tube conditioning

ABSTRACT

Various methods and systems are provided for x-ray tube conditioning for a computed tomography imaging method. In one embodiment, x-ray may be generated in an x-ray tube of a radiation source prior to a diagnostic scan to warmup the x-ray tube to a desired temperature for the diagnostic scan. The power delivered to the x-ray tube during warmup may be adjusted in a closed loop system based on an initial temperature of the x-ray tube and the desired temperature for the diagnostic scan. During tube warmup, by placing a blocking plate coupled to a collimator blade in a path of the x-ray beam, the x-ray beam may be blocked from exiting a collimator.

FIELD

Embodiments of the subject matter disclosed herein relate to diagnosticmedical imaging, and more particularly, to x-ray tube conditioning forcomputed tomography imaging method.

BACKGROUND

Noninvasive imaging modalities may transmit energy in the form ofradiation into an imaging subject. Based on the transmitted energy,images may be subsequently generated indicative of the structural orfunctional information internal to the imaging subject. In computedtomography (CT) imaging, radiation transmits from a radiation source toa detector through the imaging subject. The X-Ray tubes that power CTsystems generate x-rays by accelerating and focusing a high-energy beamof electrons onto a rotating target. As individual electrons strike thetarget, the energy released by interacting with the atoms of the targetproduces x-ray photons isotropically under a polychromatic spectrum, amaximum energy of the x-ray photons matching that of the incidentelectrons. The x-ray photons leave the tube through a window thatdefines an x-ray beam. During a scan, x-rays emitted from the x-raysource and attenuated by the imaging subject are collected or detectedby a detector and used to reconstruct a diagnostic image.

Prior to an x-ray exposure for a diagnostic scan of the imaging subject,the temperature of the x-ray tube may be increased to a desired, highertemperature range. In the desired temperature range, the target materialmay be ductile where the material is stronger and can withstand a shockup to the melting point of the target material relative to a focal spoton the target material where all beam energy is deposited. At thedesired temperature range, a higher power may be used for the x-ray tubewithout degrading the target material. Use of a higher power may alsoresult in an improved image quality. Below the desired temperaturerange, the target material may be brittle whereby a high-energy electronbeam impinging on the target may result in stress fractures such that atarget degradation might ensue. Above the desired temperature range, thetarget material may melt when it receives additional energy, which mayetch the target track at the focal spot falls.

Prior to a diagnostic scanning, a tube conditioning procedure such astube warmup may be carried out to raise the target temperature to itsdesired operating temperature range. An effective way to warm up thetube is to generate x-rays prior to the scan. A tube warmup proceduremay include a pre-defined sequence of low-power, long exposures thatdeliver energy to the x-ray tube over time to gradually warm up thetarget above brittle mode and into ductile mode. There is a need for areliable and fast tube warm up routine ensuring reliable diagnosticoutcomes with consistent image quality of diagnostic images withoutdegradation of the target material.

BRIEF DESCRIPTION

In one embodiment, a method for an imaging system, comprises: prior to adiagnostic scan, generating x-ray in an x-ray tube of a radiation sourceto condition the x-ray tube that is adjusted based on an initialtemperature of the x-ray tube and a desired temperature of the x-raytube for the diagnostic scan.

It should be understood that the brief description above is provided tointroduce in simplified form a selection of concepts that are furtherdescribed in the detailed description. It is not meant to identify keyor essential features of the claimed subject matter, the scope of whichis defined uniquely by the claims that follow the detailed description.Furthermore, the claimed subject matter is not limited toimplementations that solve any disadvantages noted above or in any partof this disclosure.

BRIEF DESCRIPTION OF THE DRAWINGS

The present invention will be better understood from reading thefollowing description of non-limiting embodiments, with reference to theattached drawings, wherein below:

FIG. 1 shows a pictorial view of an imaging system according to anembodiment of the invention.

FIG. 2 shows a block schematic diagram of an exemplary imaging systemaccording to an embodiment of the invention.

FIG. 3 shows an axonometric view of an example integrated filterassembly including a carriage, a hardening filter, and a plurality ofbowtie filters.

FIG. 4A shows a collimation arrangement for an x-ray beam of a firstsize.

FIG. 4B shows the collimation arrangement of FIG. 4A for an x-ray beamof a second size.

FIG. 4C shows the collimation arrangement of FIG. 4A for an x-ray beamof a third size.

FIG. 4D shows the collimation arrangement of FIG. 4A for an x-ray beamof a fourth size.

FIG. 4E shows the collimation arrangement of FIG. 4A for an x-ray beamof a fifth size.

FIG. 5A shows a first position of a filter assembly with three bowtiefilters and a hardening filter.

FIG. 5B shows a second position of the filter assembly of FIG. 5A.

FIG. 5C shows a third position of the filter assembly of FIG. 5A.

FIG. 5D shows a fourth position of the filter assembly of FIG. 5A.

FIG. 6 shows a flow chart of an example method for imaging usingmultiple filters included in the integrated filter assembly.

FIG. 7 shows a collimator blade including a blocking plate.

FIG. 8A shows a first position of a collimation arrangement for an x-raybeam including a blocking plate.

FIG. 8B shows a second position of a collimation arrangement for anx-ray beam including a blocking plate.

FIG. 9 shows a flow chart of an example method for conditioning an x-raytube prior to a diagnostic scan.

FIG. 10 shows a block diagram illustrating an example open-loop controlof x-ray tube temperature prior to a scan.

FIG. 11 shows a flow chart of an example method of using a scout scanfor x-ray tube conditioning prior to a diagnostic scan.

FIG. 12 shows a block diagram illustrating a guided selection of a scoutscan protocol.

FIG. 13 shows an example plot of variation in x-ray tube temperatureduring a scout scan and a diagnostic scan.

DETAILED DESCRIPTION

The following description relates to various embodiments of x-rayimaging of a subject. In particular, systems and methods are providedfor CT imaging using one or more of a hardening filter and bowtiefilters. FIGS. 1-2 show an example embodiment of an imaging system,wherein the one or more filters are positioned between the radiationsource and the imaging subject. Different filters may be selected basedon the anatomy of the imaging subject being imaged. FIG. 3 shows anexample of an integrated filter assembly including a carriage, ahardening filter, and a plurality of bowtie filters which may bepositioned to adjust a spatial distribution and condition the beamreaching the subject. As an example, in a single carriage, two bowtiefilters may be positioned next to each other with a hardening filteralso coupled to the same carriage between the two bowtie filters. Asingle bowtie filter or a combination of a hardening filter and a bowtiefilter may be positioned in a path of the beam by moving the carriagealong an axis perpendicular to the beam. FIGS. 5A-5D show variouspositions of an example filter assembly with three bowtie filters and ahardening filter. A size of the x-ray beam passing through one or morefilters and reaching the subject may be collimated based on a selectedaperture size as shown in FIGS. 4A-4E. During conditioning of the x-raytube prior to a diagnostic scan, a blocking plate, as shown in FIGS. 7and 8A-8B may be used to block x-ray beam from passing through thecollimator and reaching an imaging subject. FIG. 6 shows an examplemethod for imaging a subject using one or more filters included in theintegrated filter assembly. Example methods for conditioning an x-raytube are shown in FIGS. 8 and 11. An example of closed-loop control ofx-ray target temperature as part of the x-ray tube conditioning approachis shown in FIG. 10. A block diagram illustrating a guided selection ofa scout scan protocol using an algorithm is shown in FIG. 12. An exampleplot of variation in x-ray tube temperature during a scout scan and adiagnostic scan is shown in FIG. 13.

Though a CT system is described by way of example, it should beunderstood that the present techniques may also be useful when appliedto images acquired using other imaging modalities, such astomosynthesis, C-arm angiography, and so forth. The present discussionof a CT imaging modality is provided merely as an example of onesuitable imaging modality.

Various embodiments may be implemented in connection with differenttypes of imaging systems. For example, various embodiments may beimplemented in connection with a CT imaging system in which a radiationsource projects a fan- or cone-shaped beam that is collimated to liewithin an x-y plane of a Cartesian coordinate system and generallyreferred to as an “imaging plane.” The x-ray beam passes through animaging subject, such as a patient. The beam, after being attenuated bythe imaging subject, impinges upon an array of radiation detectors. Theintensity of the attenuated radiation beam received at the detectorarray is dependent upon the attenuation of an x-ray beam by the imagingsubject. Each detector element of the array produces a separateelectrical signal that is a measurement of the beam intensity at thedetector location. The intensity measurements from all the detectors areacquired separately to produce a transmission profile.

In third-generation CT systems, the radiation source and the detectorarray are rotated with a gantry within the imaging plane and around anobject (such as a region of the subject) to be imaged such that theangle at which the x-ray beam intersects the imaging subject constantlychanges. A complete gantry rotation occurs when the gantry concludes onefull 360 degree revolution. A group of x-ray attenuation measurements(e.g., projection data) from the detector array at one gantry angle isreferred to as a “view.” A view is, therefore, each incremental positionof the gantry. A “scan” of the object comprises a set of views made atdifferent gantry angles, or view angles, during one revolution of thex-ray source and detector.

In an axial diagnostic scan, the projection data is processed toconstruct an image that corresponds to a two-dimensional slice takenthrough the imaging subject. A scout scan (also referred herein aslocalizer scan) provides a projection view along a longitudinal axis ofthe imaging subject and generally provides aggregations each includinginternal structures of the subject. One method for reconstructing animage from a set of projection data is referred to in the art as afiltered backprojection technique. This process converts the attenuationmeasurements from a scan into integers called “CT numbers” or“Hounsfield units” (HU), which are used to control the brightness of acorresponding pixel on a display.

Beam characteristics such as size, shape, and energy may be differentfor a scout scan (also referred herein as localizer scan) and adiagnostics scan. During certain scout scans and diagnostic scans, it isdesired to use a higher power x-ray source. The higher power improvesthe quality of the diagnostic scan and increases thermal stability ofthe x-ray tube including the target. However, an increase in the x-raypower, may increase in x-ray radiation exposure for a patient. Thehardening filter may be used in the path of the beam to attenuate thebeam and reduce the energy of the x-ray beam prior to it entering thepatient's body. The hardening filter along with a bowtie filter may bespecifically desired to be used during smaller beams (lower beamcoverage) while scans with larger beam coverage may solely use a bowtiefilter. The hardening filter and the bowtie filters may be mounted onseparate carriages which can be moved in and out of the beam as desired.However, adding multiple carriages will add cost and complexity to theapparatus. Also, the time to complete scans may be longer due to theneed to move carriages in and out of the beam between sections of ascan. Therefore, according to embodiments disclosed herein, a singleintegrated filter assembly may in incorporated including a carriage, ahardening filter, and a plurality of bowtie filters. Based on the scansetup, one or more filters from the carriage may be placed in the pathof the beam. By including multiple bowtie and hardening filters in asingle integrated filter assembly, reliability of the set up may beincreased while cost and complexity of the setup may be decreased.

FIG. 1 illustrates an exemplary CT system 100 configured to allow fastand iterative image reconstruction. Particularly, the CT system 100 isconfigured to image a subject 112 such as a patient, an inanimateobject, one or more manufactured parts, and/or foreign objects such asdental implants, stents, and/or contrast agents present within the bodyplaced on a movable table 228. In one embodiment, the CT system 100includes a gantry 102, which in turn, may further include at least onex-ray radiation source 104 configured to project a beam of x-rayradiation 106 for use in imaging the subject 112. The x-ray radiationsource 104 includes a x-ray tube and a target. The x-ray tube generatex-rays by accelerating and focusing a high-energy beam of electrons ontoa rotating target. As individual electrons strike the target, the energyreleased by interacting with the atoms of the target produces x-rayphotons isotropically under a polychromatic spectrum, a maximum energyof the x-ray photons matching that of the incident electrons. The x-rayphotons leave the tube through a window that defines an x-ray beam. Thebeam can then be collimated and conditioned using collimator blades andfilter(s).

Specifically, the radiation source 104 is configured to project thex-rays 106 towards a detector array 108 positioned on the opposite sideof the gantry 102. Although FIG. 1 depicts only a single radiationsource 104, in certain embodiments, multiple radiation sources may beemployed to project a plurality of x-rays 106 for acquiring projectiondata corresponding to the subject 112 at different energy levels. Theradiation source may include an x-ray target manufactured of graphiteand metal.

In certain embodiments, the CT system 100 further includes an imageprocessing unit 110 configured to reconstruct images of a target volumeof the subject 112 using an iterative or analytic image reconstructionmethod. For example, the image processing unit 110 may use an analyticimage reconstruction approach such as filtered backprojection (FBP) toreconstruct images of a target volume of the subject 112. As anotherexample, the image processing unit 110 may use an iterative imagereconstruction approach such as advanced statistical iterativereconstruction (ASIR), conjugate gradient (CG), maximum likelihoodexpectation maximization (MLEM), model-based iterative reconstruction(MBIR), and so on to reconstruct images of a target volume of thesubject 112.

FIG. 2 illustrates an exemplary imaging system 200 similar to the CTsystem 100 of FIG. 1. In accordance with aspects of the presentdisclosure, the system 200 is configured to perform automatic exposurecontrol responsive to user input. In one embodiment, the system 200includes the detector array 108 (see FIG. 1). The detector array 108further includes a plurality of detector elements 202 that togethersense the x-ray beam 106 (see FIG. 1) that pass through a subject 204such as a patient to acquire corresponding projection data. Accordingly,in one embodiment, the detector array 108 is fabricated in a multi-sliceconfiguration including the plurality of rows of cells or detectorelements 202. In such a configuration, one or more additional rows ofthe detector elements 202 are arranged in a parallel configuration foracquiring the projection data.

A filter carriage 240 may be mounted within gantry 102 between radiatorsource 104 and the subject 204. The carriage 240 may travel in and outof the beam in the z-direction while the beam is substantially in they-direction. Two different bowtie filters, a first bowtie filter 241 anda second bowtie filter 242 are shown in FIG. 2 as an example. The firstbowtie filter 241 is housed within a first slot formed in a cavity ofthe carriage and wherein the second bowtie filter 242 is housed within asecond slot formed in the cavity of the carriage, the first slotseparated from the second slot via a tab. The bowtie filters are shownhere in rectangular shape as an example. Each and every bowtie filter isrigid and non-deformable. The bowtie filters may alternatively havedifferent shapes and material constructions to provide proper x-rayspecial spectrum for imaging various types of anatomies. A hardeningfilter 243 is shown coupled to the carriage 240 between the two bowtiefilters 241 and 242. The hardening filter 243 may at least partiallyoverlap with each of the first bowtie filter 241 and the second bowtiefilter 242. In one example, the hardening filter only partially overlapswith each of the first bowtie filter 241 and the second bowtie filter242. In another example, the hardening filter 243 may completely overlapwith one of the first bowtie filter 241 and the second bowtie filter242. The hardening filter 243 includes each of a rectangular supportstructure, and one or more rectangular metallic sheets stacked under thesupport structure. The rectangular support structure may be made ofaluminum and the one or more rectangular metallic sheets may be made ofcopper with each of the one or more rectangular metallic sheets having adifferent thickness. An example of a carriage including a plurality offilters is shown in FIG. 3.

In this example, the x-ray beam 106 passes through the hardening filter243 and the second bowtie filter 242. However, the carriage 240 may bemoved to a position such that the beam may pass through a bowtie filter(first or second) and not through the hardening filter. As an example,if the carriage 240 is moved further towards the left, the beam maysolely pass through the second bowtie filter 243. In this way, it ispossible to pass the beam through a bowtie filter and each of ahardening filter and a bowtie filter.

The bowtie filter may change the spatial distribution of the radiationbeam in the axial plane of the imaging subject (such as a patient). Forexample, the re-distributed radiation beam may have higher energy at thecenter and lower energy at the periphery of the subject. Each of thebowtie filters may be designed to image a specific anatomy or section ofthe human body, such as head, chest, and abdomen. During imaging, one ofthe bowtie filters may be selected based on the anatomy of the subjectto be scanned, and the selected filter may be placed into the radiationbeam path. Responsive to a change in the anatomy, the filter may bechanged from one to another. Based on a nature of the scan, the carriagemay be positioned such that the hardening filter may or may not beplaced in the radiation beam path. The hardening filter may attenuatethe beam and remove low energy components thereby conditioning the beamfor specific scans such as a scout scan. Example arrangement of thefilters in the filter housing is shown in FIGS. 5A-5D.

A filter driving system, such as the filter driving system 590 shown inFIG. 5, may be coupled to the carriage 240 to move the one or morefilters into and out of the radiation beam path. In one embodiment, amotor may couple the filters in the carriage through a shaft. The bowtiefilters may be switched from one to another and/or a hardening filtermay be introduced or removed from the beam path by translating thefilters along the shaft by rotating the shaft with a motor. One of thefilters may be selected and translated into the x-ray beam between theradiation source and the imaging subject to image a specific section ofthe human body. Computing device 216 may send command to the motor ofthe filter driving system to move the selected filter in to theradiation beam. The filter driving system may also send filter positioninformation back to the computing device 216.

In certain embodiments, the system 200 is configured to traversedifferent angular positions around the subject 204 for acquiring desiredprojection data. Accordingly, the gantry 102 and the components mountedthereon (such as the radiation source 104, the filter housing 240, andthe detector 202) may be configured to rotate about a center of rotation206 for acquiring the projection data, for example, at different energylevels. Alternatively, in embodiments where a projection angle relativeto the subject 204 varies as a function of time, the mounted componentsmay be configured to move along a general curve rather than along asegment of a circle.

In one embodiment, the system 200 includes a control mechanism 208 tocontrol movement of the components such as rotation of the gantry 102and the operation of the x-ray radiation source 104. In certainembodiments, the control mechanism 208 further includes an x-raycontroller 210 configured to provide power and timing signals to theradiation source 104. Additionally, the control mechanism 208 includes agantry motor controller 212 configured to control a rotational speedand/or position of the gantry 102 based on imaging requirements.

In certain embodiments, the control mechanism 208 further includes adata acquisition system (DAS) 214 configured to sample analog datareceived from the detector elements 202 and convert the analog data todigital signals for subsequent processing. The data sampled anddigitized by the DAS 214 is transmitted to a computing device (alsoreferred to as processor) 216. In one example, the computing device 216stores the data in a storage device 218. The storage device 218, forexample, may include a hard disk drive, a floppy disk drive, a compactdisk-read/write (CD-R/W) drive, a Digital Versatile Disc (DVD) drive, aflash drive, and/or a solid-state storage device.

Additionally, the computing device 216 provides commands and parametersto one or more of the DAS 214, the x-ray controller 210, and the gantrymotor controller 212 for controlling system operations such as dataacquisition and/or processing. In certain embodiments, the computingdevice 216 controls system operations based on operator input. Thecomputing device 216 receives the operator input, for example, includingcommands and/or scanning parameters via an operator console 220operatively coupled to the computing device 216. The operator console220 may include a keyboard or a touchscreen to allow the operator tospecify the commands and/or scanning parameters.

Although FIG. 2 illustrates only one operator console 220, more than oneoperator console may be coupled to the system 200, for example, forinputting or outputting system parameters, requesting examinations,and/or viewing images. Further, in certain embodiments, the system 200may be coupled to multiple displays, printers, workstations, and/orsimilar devices located either locally or remotely, for example, withinan institution or hospital, or in an entirely different location via oneor more configurable wired and/or wireless networks such as the Internetand/or virtual private networks.

In one embodiment, for example, the system 200 either includes, or iscoupled to a picture archiving and communications system (PACS) 224. Inan exemplary implementation, the PACS 224 is further coupled to a remotesystem such as a radiology department information system, hospitalinformation system, and/or to an internal or external network (notshown) to allow operators at different locations to supply commands andparameters and/or gain access to the image data.

The computing device 216 uses the operator-supplied and/orsystem-defined commands and parameters to operate a table motorcontroller 226, which in turn, may control a motorized table 228.Particularly, the table motor controller 226 moves the table 228 forappropriately positioning the subject 204 in the gantry 102 foracquiring projection data corresponding to the target volume of thesubject 204.

As previously noted, the DAS 214 samples and digitizes the projectiondata acquired by the detector elements 202. Subsequently, an imagereconstructor 230 uses the sampled and digitized x-ray data to performhigh-speed reconstruction. Although FIG. 2 illustrates the imagereconstructor 230 as a separate entity, in certain embodiments, theimage reconstructor 230 may form part of the computing device 216.Alternatively, the image reconstructor 230 may be absent from the system200 and instead the computing device 216 may perform one or morefunctions of the image reconstructor 230. Moreover, the imagereconstructor 230 may be located locally or remotely, and the imagereconstructor 230 may be operatively connected to the system 100 using awired or wireless network. Particularly, one exemplary embodiment mayuse computing resources in a “cloud” network cluster for the imagereconstructor 230.

In one embodiment, the image reconstructor 230 stores the imagesreconstructed in the storage device 218. Alternatively, the imagereconstructor 230 transmits the reconstructed images to the computingdevice 216 for generating useful patient information for diagnosis andevaluation. In certain embodiments, the computing device 216 transmitsthe reconstructed images and/or the patient information to a display 232communicatively coupled to the computing device 216 and/or the imagereconstructor 230.

FIG. 3 shows an axonometric view 300 of an example integrated filterassembly 315. The filter assembly 315 may include a rectangular carriage318. In one example, carriage 318 may be the carriage 240 in FIG. 2. Thecarriage 318 may include a first slot 321 and a second slot 323 formedlength-wise within a cavity of the carriage 318. The first slot 321 maybe separated from the second slot 323 via a tab 333. In one example,each of the two slots 321 and 323 may extend through the entire lengthof the carriage 318. In another example, each of the two slots 321 and323 may partially extend through the length of the carriage 318.

A first bowtie filter 320 may be housed within the first lot 321 while asecond bowtie filter 322 may be housed in the second slot 323. In oneexample, the first bowtie filter 320 and the second bowtie filter 322may be positioned next to each other but not in contact. In anotherexample, the first bowtie filter 320 and the second bowtie filter 322may be positioned next to each other in face-sharing contact. Each ofthe first bowtie filter 320 and the second bowtie filter 322 may beshaped as a “bowtie” with a first, straight long side and a second,parallel long side including a central ridge. In one example, the firstbowtie filter 320 and the second bowtie filter 322 may be of the samesize (such as width, length, thickness, etc.) In another example, thefirst bowtie filter 320 and the second bowtie filter 322 may be ofdifferent sizes (such as width, length, thickness). Each of the firstbowtie filter 320 and the second bowtie-filter 322 may be formed ofgraphite. A bowtie filter may be used to adjust spatial distribution ofan x-ray beam 342 passing through the filter and the size of a bowtiefilter governs a level of spatial distribution adjustments made to thex-ray beam 342 passing through the filter. The carriage 318 may includecut-outs 335 on side wall through which a bowtie filter may be visible.As shown in this example, the second bowtie filter 322 may be co-planerwith a side wall and cut-out 335 of the carriage 318. The bowtie filtersmay be secured inside their respective slots via nuts and bolts.

A hardening filter 302 may be coupled to the carriage 318 between thefirst bowtie filter 320 and the second bowtie filter 322. The hardeningfilter 302 may be embedded in a recess 345 between the first bowtiefilter 320 and the second bowtie filter 322. The length of the hardeningfilter 302 may be higher than or equal to the length of each of thefirst bowtie filter 320 and the second bowtie filter 322. However, thewidth of the hardening filter 302 may be narrower than the width of eachof the first bowtie filter 320 and the second bowtie filter 322. As therectangular hardening filter 302 is positioned between the first bowtiefilter 320 and the second bowtie filter 322, the hardening filter 302may at least partly overlap with each of the first bowtie filter 320 andthe second bowtie filter 322 and may be in face sharing contact with thetop/side surfaces of the bowtie filters.

The hardening filter 302 may include a support structure 304, and one ormore metallic sheets underneath the support structure 304. In thisexample, a first metallic sheet 306 and a second metallic sheet 308 maybe positioned under the support structure 304. Each of the firstmetallic sheet 306, the second metallic sheet 308, and the supportstructure 304 may be stacked together and bolted at each end to thecarriage 318 via a plurality of bolts 312. In this example, a pluralityof concentric holes are formed on two ends of each of the first metallicsheet 306, the second metallic sheet 308, and the support structure 304and each bolt (used to attach the layers of the hardening filter 304 tothe carriage 318) may pass through each of the concentric holes presentin each layer. As an example, one end of the hardening filter 302 may beattached to the tab 333 of the carriage 318. In one example, the supportstructure 304 may be made of a metal such as aluminum, and firstmetallic sheet 306 and the second metallic sheet 308 may be made of asame metal or different metals. Copper may be used to form one or bothof the first metallic sheet 306 and the second metallic sheet 308.

The hardening filter 302 may be used to intercept lower energyradiation, thereby attenuating and “hardening” the x-ray beam 342passing through the hardening filter 302. The degree of beam attenuationmay depend on one or more of a number of attenuation layers (such asmetallic sheets), the thickness of each attenuation layer, the materialsused in the attenuation layers, and the overall size of the attenuationlayers.

As an example, when using thinner or weaker sheets of hardening materialin 302, the support plate 304 may be used to limit deflection of 302 dueto gantry rotational forces which may act to bend the middle of thehardening material. In this embodiment, the support plate is positionedoutside of the cross-sectional area of the hardened x-ray beam that isused for imaging. In this way, the hardening filter may be solelyaccounted for in hardening the imaging x-ray beam while beingmechanically strengthened by the support plate proximal to the areawhere the imaging beam passes through the hardening filter. Furthermore,the support plate may be made from a stiff but lightweight material suchas aluminum to minimize excess x-ray scatter near the hardening filter.

An aluminum filter 324 may be coupled to the underside of the carriage318 and may extend along the entire lower surface of the carriage 318.The aluminum filter may further condition the x-ray beam 342 after thebeam has passed through one or more of the hardening filter and bowtiefilters.

During an imaging, an x-ray beam 342 may first pass through thehardening filter 302 followed by a bowtie filter and then the aluminumfilter 324. The carriage 318 may be moved along a directionperpendicular to that of the beam 342, as shown by arrows 340 toposition the beam on a bowtie filter and the hardening filter 302. Alevel of beam attenuation and spatial distribution may be adjusted byselecting a combination of hardening filter 302 and bowtie filters. Inone example, the carriage may be positioned such that the beam passesthrough the hardening filter 302 and the first bowtie filter 320, thebeam proximal to an edge of the first bowtie filter overlapping with thehardening filter 302. In another example, the carriage may be positionedsuch that the beam passes the first bowtie filter 320 only, the beamproximal to another edge of the first bowtie filter not overlapping withthe hardening filter 302. In yet another example, the carriage may bepositioned such that the beam passes through the hardening filter 302and the second bowtie filter 322, the beam proximal to an edge of thesecond bowtie filter 322 overlapping with the hardening filter 302. In afurther example, the carriage may be positioned such that the beampasses the second bowtie filter 322 only, the beam proximal to anotheredge of the second bowtie filter not overlapping with the hardeningfilter 302. After passing through one or more of the hardening filter302 and the bowtie filters, the beam may always pass through thealuminum filter 324 before entering a subject that is scanned.

Attenuation of the beam via a hardening filter may be specificallydesired during a scout scan which may precede a diagnostic scan. Duringa diagnostic scan, a bowtie filter without the hardening filter may beused for diagnostic scans. Typically, for a scout scan a smaller beam(coverage) may be used relative to the beam size used for diagnosticscans. The smaller beam may completely pass through the hardening filter302 which is narrower than a bowtie filter. By incorporating thehardening filter with the bowtie filter, a single carriage may be usedfor both scout scans and diagnostic scans, thereby reducing the numberof components and the time needed to switch between carriages during ascout scan and a successive diagnostic scan. Also, by using a hardeningfilter, a higher power x-ray source with increased x-ray tubetemperature may be used during a scan without increasing radiationexposure of the subject. The higher power may improve the quality of thescout scan and/or subsequent diagnostic scans and improve thermalstability of the x-ray tube including the target. The consistentlyhigher temperature of the x-ray tube target may contribute to long-termreliability of the device as it remains closer to an optimal operatingtemperature; fewer temperature cycles of the internal parts contributeto better reliability.

In this way, FIGS. 1-3 provide for an imaging system, comprising: agantry for receiving an imaging subject, a radiation source positionedin the gantry for emitting radiation exposure, a detector positioned onthe opposite of the gantry relative to the radiation source, a motorizedtable for moving the imaging subject within the gantry, a computationdevice with instructions stored in a non-transient memory, a filtercarriage mounted to the gantry, a first bowtie filter, a second bowtiefilter, and a hardening filter positioned in the filter carriage, thehardening filter mounted in between the first bowtie filter and thesecond bowtie filter and partially overlapping with each of the firstbowtie filter and the second bowtie filter, and a filter driving systemfor switching filters by moving one or more of the first bowtie filter,the second bowtie filter, and the hardening filter into or out of theradiation beam.

FIGS. 4A-4E show a cross-section of collimation arrangement 412 for anx-ray beam. The collimation arrangement 412 may include the integratedfilter assembly 315 of FIG. 3. The integrated filter assembly 315 mayinclude a hardening filter 302, a first bowtie filter 320, a secondbowtie filter 322, and an aluminum filter 324. An x-ray beam may passthrough a gap (aperture) formed between a first collimator blade 408 anda second collimator blade 410 after passing through the integratedfilter assembly 315. Each of the first collimator blade 408 and thesecond collimator blade 410 may be formed from lead or anotherattenuating material like tungsten which may adsorb any radiation itencounters. After passing through the gap between the first collimatorblade 408 and the second collimator blade 410, the x-ray beam may exitthe collimation arrangement 412 (a collimator) via a collimator outputport (opening) 418. The gap between the first collimator blade 408 andthe second collimator blade 410 may correspond to the desired beamcoverage. A beam of different sizes may be adjusted based on the scandesired and characteristic of the subject (such as the anatomy to bescanned). As such, a size of beam used in a scout scan may be smallerthan a size of beam used for a diagnostic scan of a specific anatomy. Inthe example embodiments of FIGS. 4A-4E, specific beam widths of 5 mm, 10mm, 15 mm, 20 mm, and 25 mm are shown, however beams of other widths maybe used in other embodiments.

In the first embodiment 400 of the collimation arrangement 412, thedesired x-ray beam size is 5 mm. The carriage 302 is positioned in a waythat the x-ray beam 415 passes through each of hardening filter 302, thefirst bowtie filter 320, and the aluminum filter. After exiting theintegrated filter assembly 315, the x-ray beam 415 is collimated to asize of 5 mm as it then passes through an aperture 414 between firstcollimator blade 408 and a second collimator blade 410. By adjusting therelative positioning of the first collimator blade 408 and the secondcollimator blade 410, the size of the aperture 414 may be adapted to 5mm. After passing through the integrated filter assembly 315 wherein thex-ray beam is conditioned as the beam passes through the filters, thebeam is collimated to the desired size of 5 mm via the aperture 414. Thex-ray beam 415 exiting the aperture 414 may then reach the subject to bescanned.

In the second embodiment 420 of the collimation arrangement 412, thedesired x-ray beam size is 10 mm. The carriage 302 is positioned in away that allows the x-ray beam 425 to pass through each of hardeningfilter 302, the first bowtie filter 320, and the aluminum filter. Afterexiting the integrated filter assembly 315, the x-ray beam 425 iscollimated to a size of 10 mm as it then passes through an aperture 424between first collimator blade 408 and a second collimator blade 410. Byadjusting the relative positioning of the first collimator blade 408 andthe second collimator blade 410, the size of the aperture 424 may beadapted to 10 mm. After passing through the integrated filter assembly315 wherein the x-ray beam 425 is conditioned as the beam passes throughthe filters, the beam is collimated to the desired size of 10 mm via theaperture 424. The x-ray beam 425 exiting the aperture 424 may then reachthe subject to be scanned.

In the third embodiment 440 of the collimation arrangement 412, thedesired x-ray beam size is 15 mm. The carriage 302 is positioned in away that the x-ray beam 445 passes through each of hardening filter 302,the first bowtie filter 320, and the aluminum filter. After exiting theintegrated filter assembly 315, the x-ray beam 445 is collimated to asize of 15 mm as it then passes through an aperture 444 between firstcollimator blade 408 and a second collimator blade 410. By adjusting therelative positioning of the first collimator blade 408 and the secondcollimator blade 410, the size of the aperture 444 may be adapted to 15mm. After passing through the integrated filter assembly 315 wherein thex-ray beam is conditioned as the beam passes through the filters, thebeam is collimated to the desired size of 15 mm via the aperture 444.The x-ray beam 445 exiting the aperture 444 may then reach the subjectto be scanned.

In the fourth embodiment 460 of the collimation arrangement 412, thedesired x-ray beam size is 20 mm. The carriage 302 is positioned in away that the x-ray beam 465 passes through each of hardening filter 302,the first bowtie filter 320, and the aluminum filter. After exiting theintegrated filter assembly 315, the x-ray beam 465 is collimated to asize of 20 mm as it then passes through an aperture 464 between firstcollimator blade 408 and a second collimator blade 410. By adjusting therelative positioning of the first collimator blade 408 and the secondcollimator blade 410, the size of the aperture 464 may be adapted to 20mm. After passing through the integrated filter assembly 315 wherein thex-ray beam is conditioned as the beam passes through the filters, thebeam is collimated to the desired size of 20 mm via the aperture 464.The x-ray beam exiting the aperture 464 may then reach the subject to bescanned.

In the fifth embodiment 480 of the collimation arrangement 412, thedesired x-ray beam size is 25 mm. The carriage 302 is positioned in away that the x-ray beam 485 passes through each of hardening filter 302,the first bowtie filter 320, and the aluminum filter. After exiting theintegrated filter assembly 315, the x-ray beam 485 is collimated to asize of 25 mm as it then passes through an aperture 484 between firstcollimator blade 408 and a second collimator blade 410. By adjusting therelative positioning of the first collimator blade 408 and the secondcollimator blade 410, the size of the aperture 484 may be adapted to 25mm. After passing through the integrated filter assembly 315 wherein thex-ray beam is conditioned as the beam passes through the filters, thebeam is collimated to the desired size of 25 mm via the aperture 484.The x-ray beam exiting the aperture 484 may then reach the subject to bescanned.

FIGS. 5A-5D show an example configuration of a filter assembly 500 withthree filters 505, 506, and 507 within filter housing 510. As anexample, each of the three filters 505, 506, and 507 may be bowtiefilters. In this example, the first filter 508 and the second filter 506are positioned together in a carriage 504. A hardening filter 513 may becoupled to the carriage 504 between the first filter 508 and the secondfilter 506. In one example, the carriage 504 may be the carriage 318 inFIG. 3.

The carriage 504 may be coupled to a ballscrew 511, and the carriage maybe translated along a first shaft 505 by rotating the first shaft with afirst motor 502. The third filter 507 may be coupled to a ballscrew 512and may be translated along a second shaft 509 by rotating the secondshaft with a second motor 503. A localized clearance feature (not shown)is present in carriage 504 to avert interference of the second shaft 509with the carriage 504 as the carriage 504 translates along the firstshaft 505. The direction of the x-ray beam (such as x-ray radiation 106of FIGS. 1-2) is indicated by 501. One of the three filters along withthe hardening filter 513 may be selectively translated into the beampath of the x-ray beam by rotating one or both shafts 505 and 509 viamotors 502 and 503, respectively. The first and the second shafts may bealigned in one line, and are spaced apart from each other by a gap 523.The x-ray beam 501 may transmit through the gap 523. The motor (such asmotor 503), the shaft (such as shaft 509) coupled to the motor, and thefilter (such as filter 507) coupled to the shaft may form a filterdriving system 590. The filter assembly 500 may include one or morefilter driving systems.

FIG. 5A shows a first position 520 of the filter assembly 500. The x-raybeam 501 transmits through the filter housing 510 without passingthrough any filter. The carriage 504 including the first filter 508, thesecond filter 506, and the hardening filter 513 may be located closer tothe first motor 502, and the third filter may be located closer to thesecond motor 503.

FIG. 5B shows a second position 540 of the filter assembly 500. Thex-ray beam 501 transmits though each of the hardening filter 513 and thefirst filter 508 in the filter housing 810. The filter assembly 500 maytransit from the first position 520 to the second position 540 byactuating the first motor 502 and translating the hardening filter 513and the first filter 508 (in carriage 504) into the x-ray beam path.

FIG. 5C shows a third position 560 of the filter assembly 500. The x-raybeam 501 solely transmits though the second filter 506 (without thehardening filter 513 in between) in the filter housing 810. The filterassembly 500 may transit from the first position 520 or the secondposition 540 to the third position 560 by actuating the first motor 502and translating the second filter 506 (in carriage 504) into the x-raybeam path.

FIG. 5D shows a fourth position 580 of the filter assembly 500. Thex-ray beam 501 transmits through the third filter 507 in the filterhousing 510. The filter assembly 500 may transit from any of theabove-mentioned first, second, or third position to the fourth position580 by actuating the first motor 502 to translate the carriage 504closer to the first motor 502, and subsequently or simultaneouslyactuating the second motor 503 to translate the third filter 507 intothe x-ray beam path.

Based on the instructions stored in the non-transient memory, thecomputing device (such as computing device 216 of FIG. 2) may move thefilter assembly from any one of the above positions to another positionby actuating one or more of the two motors. In one embodiment, twofilters and a hardening filter are positioned in a carriage. As oneexample, the two filters may be coupled to one shaft and driven by onemotor. As another example, one of the two filters and the hardeningfilter are coupled to one shaft and driven by one motor, and the otherof the two filters is coupled to a second shaft and driven by a secondmotor. In another embodiment, more than three filters and multiplehardening filters may be arranged within the filter housing. Forexample, the numbers of filters coupled to each shaft are the same, ifthe total number of filters in the housing is even. The numbers offilters coupled to each shaft is different, if the total number offilters in the housing is odd.

In yet another embodiment, the arrangement of the filters in the filterhousing may be based on the type of the filters. Herein, the filter typemay be determined by the section of the subject that the filter isdesigned to image. For example, the first filter used for imaging thefirst section of the subject and the second filter used or imaging thesecond section of the subject may be positioned next to each other, ifthe first section and the second section are connected. The first filterand the second filter may be positioned apart from each other (such asseparated by another filter), if the first section and the secondsection are not connected. As an example, the filter for imaging theabdomen maybe positioned next to the filter for imaging the chest, butapart from the filter for imaging the head. In this way, when the chestis imaged after imaging the abdomen, the filters may be quickly switchedfrom one to another. When the head is imaged after imaging the abdomen,the duration for filter switching may be longer, as the imaging subjectneeds to be physically moved from imaging the abdomen to imaging thehead. The hardening filter may be coupled between two filters which maybe used for a scout scan.

In other embodiments, a carriage including filters may be translatedwith any one of a rack and pinion, a belt, or a cable-driven system. Afilter driving system in the filter assembly may switch one filter toanother within two seconds. For example, the filter can be translated3-5 inches in less than two seconds by the filter driving system.

FIG. 6 shows an example method 600 for performing image scans usingmultiple filters included in an integrated filter assembly (such asintegrated filter assembly 325 in FIG. 3). Method 600 achieves imageacquisition of multiple anatomies of the imaging subject by changingfilters within a same carriage between successive scans. Method 600 andall methods described herein may be performed according to instructionsstored in the non-transitory memory in a computing device (such ascomputer 216 of FIG. 2) of the imaging system.

At 602, a subject (such as subject 204 in FIG. 2) of the imaging scansmay be positioned on a motorized table (such as table 228 in FIG. 2). Atable motor controller may move the table so that a proper section ofthe subject is within the gantry for imaging.

At 604, the routine includes determining if a scout scan is desired. Ascout scan provides a projection view along a longitudinal axis of theimaging subject and generally provides aggregations each includinginternal structures of the subject. During a scout scan, while all thecomponents of the imaging system may be maintained in a stationaryposition, the subject may be passed through the imaging system toperform a scan on the subject. A scout scan may be used to identify aregion of interest of the subject for a subsequent diagnostic scan.

If it is determined that a scout scan is desired, at 606, scanparameters may be set up for carrying out a scout scan. For example, auser may input or select the scan parameters according to a scanningprotocol or a menu. The scan parameters may include the type andsequence of the filters that are going to be used during the scan. As anexample, for a scout scan a bowtie filter along with a hardening filtermay be used for conditioning the x-ray beam used for imaging thesubject. Scan parameters may also include setting scan timing. As oneexample, the scan timing may include a start time and a duration forimaging each section.

At 608, a bowtie filter and a hardening filter may be positioned in thepath of the x-ray beam by operating a motor coupled to a carriageincluding the bowtie filter (such as bowtie filter 320 in FIG. 3) andthe hardening filter (such as hardening filter 302 in FIG. 3). Thecarriage may be moved along a shaft in a plane perpendicular to theplane of the x-ray beam to position the bowtie filter and the hardeningfilter in the beam. The controller may actuate the motor to move theshaft and the carriage to the desired position. The bowtie filter maychange the spatial distribution of the radiation beam in the axial planeof the imaging subject (such as a patient). For example, there-distributed radiation beam may have higher energy at the center andlower energy at the periphery of the subject. A hardening filter mayintercept lower energy radiations, thereby attenuating and “hardening”the beam. The hardening filter may at least partially overlap with thebowtie filter and the beam may first pass through the hardening filterand then enter the bowtie filter.

At 610, method 600 may start acquiring the dataset of the imagingsubject and simultaneously monitor the anatomy of the imaging subject.For example, the radiation source (such as 104 of FIGS. 1-2) may beactivated, and radiation exposure (such as 106 of FIGS. 1-2) of theimaging subject through the bowtie filter and the hardening filter maybe started. For a scout scan, a smallest permissible beam may be used.In one example, the beam may be 5 mm. By using a hardening filter toattenuate the beam reaching the subject, a higher power x-ray sourcewith increased x-ray tube temperature may be used during the scout scanwithout increasing radiation exposure of the subject. The higher powerimproves the quality of the diagnostic scan and improves thermalstability of the x-ray tube including the target. In one example, a 50kW x-ray power scan technique (100 kV, 500 mA) may be used.

The dataset is acquired from the detector (such as 108 of FIG. 2) uponreceiving the transmitted radiation signal from the imaging subject. Asone example, the anatomy of the imaging subject may be monitored byanalyzing the acquired dataset. As another example, the anatomy of theimaging subject may be estimated by the currently imaged location. Thecurrently imaged location may be calculated based on the startinglocation of the scan and the travel distance of the motorized table. Inone embodiment, the anatomies of the subject may be grouped in differenttypes. For example, the anatomy of a human body may be grouped based onsize, type such as the head, the chest, and the abdomen.

At 612, the routine includes determining if the scout scan has ended.The end of the scout scan may be determined based on the protocol setupat step 606. If it is determined that the scout scan has not ended, at614, the scout scan may be continued, and data may be acquired.

If it is determined that the scout scan has ended, at 616, the routineincludes determining if a diagnostic scan may is desired. As an example,a decision to carry out the diagnostic scan may be made based on theimages reconstructed from the data acquired during the scout scan. Theimage from the scout scan may be two-dimensional or three-dimensional.Based on the scout scan, a specific anatomy may be selected for adiagnostic scan. The diagnostic scan may provide a detailed image of thespecific anatomy which might not be available via the scout scan.

If at 604, it is determined that a scout scan is not desired, theroutine may directly proceed to step 616 for determining if a diagnosticscan is desired. A scout scan may not always precede a diagnostic scan.

If it is determined that a diagnostic scan is not desired and a scoutscan has been completed, at 618, the acquired dataset from the scoutscan is displayed and stored. In one embodiment, dataset acquired fromdifferent sections of the subject may be re-constructed to form animage. The acquired dataset, as well as the processed images may besaved in the storage of the imaging system and no further scans may becarried out. The routine may then end.

If it is determined that a diagnostic scan is desired, the routine mayproceed to step 620 wherein the scan parameters may be set up forcarrying out a diagnostic scan. A user may input or select the scanparameters according to a scanning protocol or a menu. The scanparameters may include the type and sequence of the filters that aregoing to be used during the scan. The type of the filters may be chosenbased on the anatomy of imaging subject that is to be imaged. Theparameters may also include setting scan timing. As one example, thescan timing may include a start time and a duration for imaging eachsection. Anatomy information of the imaging subject may be loaded to thememory of the computation device. The anatomy information may beacquired from a pre-scan. The anatomy information may be acquired fromthe prior scout scan or a localized scan. This step may also includemoving the imaging subject via the motorized table so that the propersection of the subject is within the gantry for imaging.

At 622, a contrast agent may be injected into the imaging subject. Thecontrast agent may enhance the contrast of images captured specificallyfor certain anatomies. This step is optional and the diagnostic scan maybe carried out without use of a contrast agent.

At 624, a bowtie filter may be positioned in the path of the x-ray beamby operating a motor coupled to a carriage including the bowtie filter.The type of the filter may be determined based on the anatomy of thecurrently imaged section of the subject. The carriage may be moved alonga shaft in a plane perpendicular to the plane of the x-ray beam toposition the bowtie filter in the beam. For a diagnostic scan, a largerbeam size is used and therefore a hardening filter may no longer beused. In one example, the bowtie filter used for the diagnostic scan maybe same as the bowtie filter used in the scout scan. In another example,the bowtie filter used for the diagnostic scan may be different from thebowtie filter used in the scout scan. In this way, a single carriageincluding one or more bowtie filters and a hardening filter may be usedfor both the scout scan and the diagnostic scan without the need foradditional components.

At 626, dataset of the imaging subject may be acquired andsimultaneously the anatomy of the imaging subject may be monitored. Forexample, the radiation source may be activated, and radiation exposureof the imaging subject through the selected bowtie filter may bestarted. For a diagnostic scan, a beam size of 25 mm-160 mm may be used.The dataset is acquired from the detector upon receiving the transmittedradiation signal from the imaging subject. As one example, the anatomyof the imaging subject may be monitored by analyzing the acquireddataset. As another example, the anatomy of the imaging subject may beestimated by the currently imaged location. The currently imagedlocation may be calculated based on the starting location of the scanand the travel distance of the motorized table. In one embodiment, theanatomies of the subject may be grouped in different types. For example,the anatomy of a human body may be grouped based on size, types of suchas the head, the chest, and the abdomen.

At 628, the routine includes determining if the diagnostic scan hasended. The end of the diagnostic scan may be determined based on theprotocol setup at step 620. If it is determined that the diagnostic scanhas not ended, a 630, the diagnostic scan may be continued and data maybe acquired.

If it is determined that the diagnostic scan has ended, the acquireddataset from the diagnostic scan is displayed and stored. In oneembodiment, dataset acquired from different sections of the subject maybe re-constructed to form an image. The acquired dataset, as well as theprocessed images may be saved in the storage of the imaging system andno further scans may be carried out. The routine may then end.

In this way, during a first imaging (such as a scout scan), a carriagemay be moved to position a hardening filter and a first bowtie filterhoused in the carriage in a path of a radiation beam between a radiationsource and an imaging subject and during a second imaging (such as adiagnostic scan), the carriage may be moved to move the hardening filterand the first bowtie filter out of the path of the radiation and thenposition a second bowtie filter housed in the carriage in the path ofthe radiation.

In this way, a single carriage may include one or more bowtie filter andhardening filters which may be selectively positioned in a path of anx-ray beam entering a subject without having to stack multiple carriagesand switch carriages between scans. The technical effect of attenuatinga beam reaching the subject by using a hardening filter is that a higherpowered x-ray source with increased x-ray tube temperature may be usedduring a scan without increasing radiation exposure of the subject.Overall the higher power improves the quality of the diagnostic scan andimproves thermal stability of the x-ray tube including the target.

Prior to an x-ray exposure for a diagnostic scan of the imaging subject,the temperature of the x-ray tube may be increased to a desired, highertemperature range. In the desired temperature range, the target materialmay be ductile where the material is stronger and can withstand theshock up to the melting point of the target material relative to a focalspot on the target material where all beam energy is deposited. At thedesired temperature range, a higher power may be used for the x-ray tubewithout degrading the target material. Use of a higher power may alsoresult in an improved image quality for a diagnostic scan.

A desired range of temperature for a tungsten-alloy target may bebetween 200° C. and 300° C. After heating the target to the desiredtemperature range, the duration of time that the target remains withinthis range of temperature is a function of the cooling characteristicsof the x-ray tube and of the frequency and nature of the exposures thatdeliver heat to the tube. As such, a thermal management system for thex-ray tube is designed to efficiently remove heat from the tube after anexposure is completed, to return the tube to below 300° C. However, ifthe tube is allowed to cool too fast for the desired patient throughput,the tube may be too cold to scan the next patient at the required powerlevel.

Therefore, a tube conditioning procedure (also referred herein as tubewarmup) may be desired to increase the tube temperature and maintain thetemperature of the target in the desired temperature range before adiagnostic scan may be performed. An effective way to warm up the tubeis to generate x-rays. A tube warmup procedure may typically consist ofa pre-defined sequence of low-power, long exposures that may deliversufficient energy over time to gradually warm up the target abovebrittle mode and into ductile mode. As such, an operator of the CTscanner may manually initiate a tube warmup before the patient entersthe room in order to avoid unnecessary radiation exposure. In order toguarantee that the target is not in brittle mode, the same warmupsequence may be used regardless of an actual (initial) state of thetube.

However, if tube conditioning is to be manually initiated by theoperator prior to each diagnostic scan, the conditioning process maycause an interruption in the workflow of the operator who attempts tocarry out a maximum possible number of scans in a day. A warmupprocedure may require an additional 3 to 5 minutes during which thepatient will have to wait outside the room to avoid unnecessaryradiation exposure. It would be challenging to maintain a high rate ofcompletion of scans if this additional tube conditioning time is to bespent between every two consecutive patients.

If scanning is continued while the target temperature has decreased tobelow the desired temperature range, a loss of image quality performancemay be observed since allowed exposures are power limited to protect thetube. Therefore, with a cooler tube, the recommended radiation dose fora desired image quality during a diagnostic scan may not be delivered.

The operator may have to manually initiate the tube warmup by using atool separate from patient scanning. While the system providesinformation to the operator as to the state of the x-ray tube, tubeconditioning may not always be part of the inherent workflow of theoperator on the system. On the other hand, conditioning may not beautomated since the operator needs to confirm that no one is in the scanroom when x-rays are turned on even for the purpose of a tube warmup.

Using fixed, pre-defined exposure sequences for tube warmup that runopen-loop may not allow control over the exact target temperature at theend of the warmup procedure. It is for instance possible to exceed thehot limit (e.g. 300° C.) at the time of the diagnostic scan. Some toolssuch as specific calibration steps (focal spot alignment, etc.) wouldalso benefit from a desired target temperatures at the end of a warmupto produce consistent results. Diagnostic scanning would also benefitfrom running at temperatures that match the system environment whendetailed calibration was initially performed and stored on the system.Repeatedly running long warmup sequences that deliver a lot of energy tothe tube may be stressful to some tube components and reduce useful tubelife. Therefore, new approaches are needed to overcome the abovechallenges centered on tube warmup consistency and ease-of-use.

Therefore, according to embodiments disclosed herein, a set of tubeconditioning approaches may be carried out to effectively warmup thetube within a shorter time while preparing the subject (such as apatient) for the scan inside the scan room. The temperature of the x-raytube may be controlled via a closed-loop control system. An initialthermal state of the tube, a desired thermal state of the tube, andduration of time available to reach the desired thermal state is used asinput, and a thermal model of the tube behavior may be used to calculatethe exposure parameters (such as voltage, current, duration of exposure)that is needed to transition the tube in the desired state. Byconsidering the initial thermal state of the tube and using aclosed-loop system, the final desired thermal state may be reachedwithout overshooting the temperature. Different end thermal states maybe selected a variety of scans (such diagnostic scanning planned atdifferent times after tube warmup is completed, or different warmupoutcomes for calibration procedures, etc.). By directly select theconditioning outcome, such as the amount of time from conditioning tosubject scanning, it may be ensured that the tube target remains in theoptimal temperature range at the time of the diagnostic exposure, whichmay vary across patient procedures, or at different times of the daywith varied patient throughput, or across different shifts or teams ofoperators.

During x-ray generation for tube warmup, an x-ray blocking plate may bepositioned in front of an exit (pre-patient) collimator aperture tocompletely block the primary x-ray beam path before the subject. In thisway, the subject can be in the room being prepared for the diagnosticscan while x-ray generation may be continued for tube conditioning. Byusing the time for tube conditioning for subject preparation, overalltime required for each subject may be reduced and more number of scansmay be incorporated within a day.

One or more scout scans may be performed prior to a diagnostic scan. Ahigher power x-ray beam may be used during a scout scan to condition thex-ray tube for an immediately subsequent diagnostic scan. By adding ahardening filter in the path of the x-ray beam reaching the subjectduring a scout scan, the beam reaching the subject may be attenuated,thereby reducing the radiation exposure of the subject. Further, thebeam collimation of the scout exposure may be significantly reduced(such as to a slit aperture) in order to reduce the portion of the x-raybeam that reaches the subject, thereby reducing the actual radiationdose received by the subject. In this way, a tube warmup can effectivelybe completed immediately before the diagnostic scan that typicallyfollows the scout scan. This allows a seamless workflow where tubeconditioning does not need to be manually performed outside of scantimes. By conditioning the tube during an actual scan, focal spotposition may be carried out consistently with reduced thermal motion,and better image quality may be achieved by matching the diagnosticscanning conditions to the way the system calibration vectors wereinitially generated. Tube warmup may also take less time since it iscarried out immediately prior to the diagnostic scan exposure withoutmuch tube cool down time in between.

FIG. 7 shows a collimator blade assembly 700 including a collimatorblade 702 and a blocking plate 704. The collimator blade 702 may be thecollimator blade 408 or 410 in FIGS. 4A-4E. A blocking plate 704 may beattached to a lower surface of the collimator blade in the x-z planewith the x-ray beam incident on the collimator blade assembly 700 in they-direction.

The blocking plate 704 may extend outside the edge of the collimatorblade 702 in one direction. The extended portion of the blocking plate704 may extend away from the edge of the collimator blade 702 forming anaperture for x-ray beam to pass through. As an example, the width of theblocking plate (x-direction) may be longer than the output port(opening) of the collimator such that the blocking plate 704 may bepositioned to completely absorb any x-rays incident on the plate,thereby blocking radiation to pass through the output port. The lengthof the blocking plate 704 (z-direction) may be equal to the length ofthe collimator blade 702.

The blocking plate 704 may completely or partially overlap with thelower surface (base) of the collimator blade 702. In this example, theblocking plate 704 is in face sharing contact with the base of thecollimator blade 702. In alternate embodiments, there may be a gapbetween the base of the collimator blade 702 and the blocking plate 704with the blocking plate 704 placed between the collimator blade 702 andthe output port of the collimator. The blocking plate 704 may be made oflead or tungsten to be able to absorb any direct or scattered x-raybeams that come in contact with it.

In this example, the upper surface (top) of the collimator blade 702 isshown to be curved which facilitates in obtaining a parallel beamprofile for x-ray beams impinging on a detector. In alternateembodiments, the upper surface of the collimator blade 702 may be flat.

FIGS. 8A-8B show a collimation arrangement 812 for an x-ray beamincluding a blocking plate. An x-ray beam may pass through a gap(aperture) formed between a first collimator blade 802 and a secondcollimator blade 804 after passing through one or more filters (such asa bowtie filter and/or a hardening filter). As an example, the firstcollimator blade may be the first collimator blade 408 in FIG. 4A-4Eand/or collimator blade 702 in FIG. 7, and the second collimator blademay be second first collimator blade 410 in FIG. 4A-4E. After passingthrough the gap between the first collimator blade 802 and the secondcollimator blade 804, the x-ray beam may exit the collimator via acollimator output port (opening) 812. The gap between the firstcollimator blade 802 and the second collimator blade 804 may correspondto the desired beam diameter.

A first blocking plate 806 may be coupled to the base of the firstcollimator blade 802 and a second blocking plate 807 may be coupled tothe base of the second collimator blade 804 to block any direct orscattered x-ray beam incident on it. The first blocking plate 806 mayextend beyond the edge of the first collimator blade 802 to effectivelyblock the x-ray beam when it is desired to block the entire x-ray beamfrom exiting the collimator via the output port.

FIG. 8A shows a first position 800 of the collimation arrangement 812.The collimation arrangement 812 may be in the first position when anx-ray beam is desired to exit the collimator and is used for scanning asubject.

The x-ray beam 806 is collimated to a desired size as it passes throughan aperture 816 between the first collimator blade 802 and the secondcollimator blade 804. By adjusting the relative positioning of the firstcollimator blade 802 and the second collimator blade 804, the size ofthe aperture 816 may be adapted to the desired beam size. The collimatedx-ray beam may then exit the collimator via the output port 812. FIG. 8Bshows a second position 800 of the collimation arrangement 812.

FIG. 8B shows a second position 850 of the collimation arrangement 812.The collimation arrangement 812 may be in the second position when it isdesired to block an x-ray beam from exiting the collimator such asduring x-ray tube conditioning. During x-ray tube conditioning (warmup)x-ray may be generated to impart energy to the x-ray tube. However, inorder to reduce radiation exposure of a subject prior to an actual scan,the x-ray may be blocked from exiting the collimator and reaching thesubject being prepared for a subsequent scan.

One or both of the first collimator blade 802 and the second collimatorblade 804 may be moved closest to each other such that the aperture(gap) 826 formed between the first collimator blade 802 and the secondcollimator blade 804 is the lowest possible and that one or more of thefirst collimator blade 802, the second collimator blade 804, the firstblocking plate 806, and the second blocking plate 807 may completelyblock the x-ray beam 808 and any secondary (scattered) radiations 816.

In this example, the first collimator blade 802 along with the firstblocking plate 806 is effectively being used to block the entire x-rayfrom reaching the output port 812 of the collimator. In this way, byattaching a separate blocking plate to the collimator blade andpositioning the blocking plate in the path of the x-ray beam, theprimary x-ray beam and scattered radiations may be blocked from reachinga subject. Therefore, during x-ray tube warmup, the subject may beprepared in the scanning room without the possibility of undesirableradiation exposure.

In this way, the systems of FIGS. 7 and 8A-8B enable a system for anx-ray collimator including a first collimator blade and a secondcollimator blade separated by a gap, the gap forming an aperture of thecollimator; and a blocking plate coupled to the first collimator blade,the blocking plate positioned in a path of an x-ray beam to block thex-ray beam from exiting the collimator during x-ray generation tocondition a x-ray tube prior to a diagnostic scan.

FIG. 9 shows an example method 900 for conditioning an x-ray tube priorto a diagnostic scan. Method 900 may be carried out after completion ofa diagnostic scan and/or upon receiving indication (such as via anoperator) that another diagnostic scan is imminent.

At 902, the routine includes determining if x-ray tube warmup is desiredprior to a scan. An x-ray tube warmup may include increasing thetemperature of the x-ray tube and the x-ray target to a desiredtemperature range. In one example, the desired temperature range may bebetween 200° C. and 300° C. An x-ray tube warm up may be desired priorto a diagnostic scan so that the target material reaches a desiredtemperature range. Below the desired temperature range, the targetmaterial may be brittle whereby a high-energy electron beam impinging onthe target may result in stress fractures such that a target failuremight ensue. Use of a higher x-ray power during a scan may result in animproved image quality.

If it is determined that an x-ray tube warmup is not desired, at 904,the current x-ray tube condition may be maintained. In one example, inthe current x-ray tube condition, x-rays may not be generated toactively heat the tube. In another example, x-ray generation in thex-ray tube may be continued without any alterations.

If it is determined that x-ray tube warmup is desired prior to a scan,at 806, an initial (current) temperature of the x-ray tube may beestimated. In one example, a thermal model may be used to estimate theinitial temperature of the x-ray tube. The initial temperature may bemolded based on ambient temperature, exposure history (such as power ofx-ray generated in the tube) over a last calibrated duration (such asover last 5 hours), and thermal properties of the x-ray tube such asheat transfer coefficient of the tube and the target. The model mayestimate a thermal state of the tube including a temperature of thetarget as the state evolves over time. As such the temperature of thetarget may be same as the temperature of the tube and other associatedcomponents. In another example, the target temperature may be differentfrom that of the tube and a separate initial target temperature andinitial tube temperature may be estimated. In another example, x-raytube temperature may be estimated based on inputs from a temperaturesensor housed in the x-ray tube.

At 908, a desired target temperature at the onset of the upcomingdiagnostic scan and the time to the start of the scan may be determined.The desired target temperature at the start of the scan and the timeremaining between the completion of the tube warmup routine and thestart of the diagnostic scan may be termed as the end criteria. The endcriteria may be built into some tools or system presets, or may beselected by the user. As an example, a user may input or select thedesired temperature according to a scanning protocol or a menu. Also,the user may input the start time of the upcoming diagnostic scan.

In one example, for patient scanning, the user and/or the system maydetermine that the tube target should be above 200° C. five minutesafter the completion of the warmup procedure. This may allow enough timeto prepare the patient, position the anatomy and prepare for a contrastinjection, while ensuring the target is still above brittle mode toavoid cold tube limits and allow the maximum available tube power forpatient imaging. In another example, the user may want to extend thetime to 200° C. (at the onset of the scan) to 10 minutes after thecompletion of the warmup procedure during conditions when more time isneeded for a different patient or a procedure before the firstdiagnostic exposure. In yet another example, a calibration tool such asfocal spot alignment may need the target to be at 330° C. one minuteafter tube warmup in order to align the spot for the average operatingtube temperature, thus optimizing operation for patient scanning, andimproving alignment consistency over time.

At 910, a blocking plate may be positioned in the collimator to block acollimator aperture. The blocking plate (such as blocking plate 806 inFIG. 8B) may be positioned in front of an exit (pre-patient) collimatoraperture. The blocking plate may be made of tungsten which may absorbany x-ray radiations coming in contact with the plate, therebyinhibiting the radiation to reach the subject. The blocking plate may bepositioned over an output port of the collimator completely blocking anaperture and the output port of the collimator, the aperture formed by agap between a first collimator blade and a second collimator blade. Theblocking plate may be coupled to a lower surface of one of the firstcollimator blade and the second collimator blade, the lower surfaceproximal to the output port of the collimator. The blocking plate mayextend beyond a first edge of the base of the first collimator blade,wherein the first edge is distal from the second collimator blade.

The blocking plate may completely overlap the collimator output port andtogether with sufficient shielding in the collimator, indirect scatteredand stray radiation escaping from the collimator assembly through theopen port may be negligible. As such, the collimator blades may bedesigned to maintain a certain minimum aperture and not completely blockthe beam. Therefore, without the presence of the blocking plate,undesired scattered radiation may escape the collimator. Therefore, byusing a separate blocking plate, x-ray beam may be completely blockedfrom reaching a subject during a tube warmup.

At 912, x-ray radiation may be initiated for tube warmup. For example,the radiation source (such as 104 of FIGS. 1-2) may be activated. Thex-ray beam may be attenuated by the blocking plate before reaching asubject. The x-ray radiation is not being used for scanning. At 914,x-ray tube temperature may be adjusted by adjusting the x-ray radiationdosage via a closed loop system. The warmup end criteria (as determinedin step 908) and the initial x-ray tube and x-ray target temperature maybe used as input to a thermal management module. The thermal managementmodule includes the model of the thermal state of the tube over time.Given the starting temperature condition and the thermal model for thex-ray tube, the thermal management module may calculate a specificsequence of warmup exposures that will result in the tube target meetingits temperature goal after the desired amount of time. The warmupsequence may be automatically tailored to the actual state of the tuberelative to the end criteria. In one example, based on the initialtarget temperature, the module may determine a magnitude of power (inthe form of tube voltage and current) to be delivered to the tube inorder to provide sufficient energy desired for warming the tube to thedesired temperature. The temperature of the target may be continuallyestimated during the warmup phase and the module may adjust the tubepower based on the current temperature of the x-ray tube.

As an example, the power delivered to the x-ray tube may be decreased ifthe temperature increases at a faster rate while the tube power may beincreased if the temperature increase rate lags. The thermal model ofthe x-ray tube is used by the module to predict the decrease intemperature in the time frame between the end of warmup and start ofdiagnostic scan, and the end temperature attained at the end of thewarmup phase may be adjusted accordingly. The temperature reached at theend of the warmup phase may be higher than the desired temperature rangeof the diagnostic scan taking into account heat loss and reduction intemperature in the time duration between the end of warmup and start ofthe diagnostic scan. As an example, if a diagnostic scan at 200° C. isto be started five minutes after the end of the warmup period, the endtemperature of the warmup period may be adjusted to 220° C. such thatupon heat dissipation over the five minutes prior to the diagnostic scan(when active heating of the tube is discontinued), the temperature atthe start of the diagnostic scan may be 200° C. In this way, by closedloop control of the x-ray tube conditioning, the desired temperature maybe reached at the onset of the diagnostic scan.

By running tube warmup no longer than needed to meet a specific goal,system efficiency may be improved. Closed-loop control may also allowimproved control of the end state (start of the diagnostic scan)precisely, thereby averting cold tube limits or tube cooling delays.Also unnecessary stress to the tube may be reduced that could otherwisereceive more energy than necessary.

Even with an adaptive tube warmup, the operator may still need toinitiate tube conditioning, as necessary, to avoid cold constraints. Itwould be desirable that the system supports a workflow where a manualtube warmup may be carried out independent of patient setup, orautomatically as part of the normal workflow on the system.

While x-ray is being generated for tube conditioning, at 916, a subject(such as subject 204 in FIG. 2) of the imaging scans may be prepared forthe upcoming diagnostic scan. The subject may be positioned on amotorized table (such as table 228 in FIG. 2). A table motor controllermay move the table so that a proper section of the subject is within thegantry for imaging. A contrast agent may be injected into the imagingsubject. The contrast agent may enhance the contrast of images capturedspecifically for certain anatomies. This step is optional and thediagnostic scan may be carried out without use of a contrast agent.Since the x-ray beam is shielded from reaching the subject, subjectpreparation may be carried out simultaneously with tube warmup withoutthe radiation exposure to the subject.

While tube warmup, the scan parameters may be set up for carrying out adiagnostic scan. A user may input or select the scan parametersaccording to a scanning protocol or a menu. The scan parameters mayinclude the type and sequence of the filters that are going to be usedduring the scan. The type of the filters may be chosen based on theanatomy of imaging subject that is to be imaged. The parameters may alsoinclude setting scan timing. As one example, the scan timing may includea start time and a duration for imaging each section. Anatomyinformation of the imaging subject may be loaded to the memory of thecomputation device. The anatomy information may be acquired from apre-scan. The anatomy information may be acquired from the prior scoutscan or a localized scan. This step may also include moving the imagingsubject via the motorized table so that the proper section of thesubject is within the gantry for imaging.

At 920, the routine includes determining if a desired target temperaturehas reached at the end of the warmup phase. As previously discussed, thedesired target temperature at the end of the warmup phase may be higherthan the desired temperature at the start of the diagnostic scan. If itis determined that the desired target temperature has not been reachedat the end of the warmup period, at 920, x-ray generation may becontinued with closed-loop control of the tube temperature.

If it is determined that the desired target temperature has reached atthe end of the warmup phase, at 921, x-ray generation may be suspendedby deactivating the radiation source. At 922, the blocking plate may bemoved out of the path of the x-ray beam and filters to be used in thediagnostic scan may be moved into the path of the beam. A bowtie filtermay be positioned in the path of the x-ray beam by operating a motorcoupled to a carriage including the bowtie filter. The type of thefilter may be determined based on the anatomy of the currently imagedsection of the subject. The carriage may be moved along a shaft in aplane perpendicular to the plane of the x-ray beam to position thebowtie filter in the beam.

At 924, x-ray generation may be initiated by activating the radiationsource and the diagnostic scan may commence according to the scanparameters set-up. In this way, prior to initiation of a diagnosticscan, a x-ray tube may be warmed up by generating x-ray in the x-raytube, a power of the generated x-ray may be adjusted via a closed loopcontrol of a temperature of the x-ray tube; and during the warm-up ofthe x-ray tube, a x-ray beam may be blocked from exiting a collimator bypositioning a blocking plate in a path of the x-ray beam.

FIG. 10 shows a block diagram 1000 illustrating open-loop control ofx-ray tube temperature prior to a scan. At 1002, an end criteria for anx-ray tube conditioning carried out prior to a scan may be definedeither as an input by the user or by the system. The end criteria mayinclude a temperature of the x-ray target at the onset of the upcomingscan and a time duration between the end of the tube conditioning (alsoreferred herein as warmup) phase and the start of the subsequent scan.

Once the end criteria is defined, at 1004, the system may calculate anamount of energy to be delivered to the x-ray tube during the warmupphase to achieve the end criteria. In order to determine the amount ofenergy to be delivered, at 1012, the system enquires a current x-raytube temperature via a thermal model and/or an x-ray tube temperaturesensor. The system may use a look-up table to determine the amount ofenergy to be delivered with the current temperature and the end criteriaas inputs and the amount of energy to be delivered to the x-ray tube asoutput.

At 1006, the system may transform the amount of energy to be deliveredto the x-ray tube into specific x-ray warmup exposure(s). The energy maybe imparted as a single, continuous, x-ray exposure or as a series ofdiscrete x-ray exposures. The power delivered in each exposure may beestimated based on the amount of energy to be delivered to the x-raytube and the duration of the exposure. Taking into account systemconstraints such as the maximum possible power that may be delivered tothe x-ray tube, the system may determine the power delivered during thetube warmup phase based on a look-up table with the amount of energy tobe delivered to the x-ray tube as input and the power to be deliveredduring each (or only) x-ray exposure.

At 1008, the user may activate a radiation source to generate x-rays inthe tube. The power of the x-rays generated may impart the amount ofenergy desired to fulfil the end criteria. During the x-ray tubeconditioning, a blocking plate may be placed within an x-ray beamcollimator tube to stop the x-ray beam from reaching the patient. At1010, the patient may be setup for the subsequent diagnostics scan andonce the end criteria is reached, the diagnostics scan may be carriedout. Alternatively, a calibration scan (with or without the presence ofa patient) may also be carried out.

Once the scan is completed, the x-ray tube is immediately prepared forthe subsequent scan of the same or next patient and the current x-raytube temperature is enquired by the system to be used for closed-looptemperature control of the x-ray tube.

As described earlier, it is desired to attain an x-ray targettemperature prior to a diagnostic scan. By operating below the desiredthermal range, the x-ray tube target material may become brittle, thusleading to an increase in the number of fissures in the target andleading to degradation of the target. By operating above the desiredthermal range, the system may overheat and cannot cool quickly enough atthe time of the diagnostic scan. Operation of the x-ray tube outside thedesired temperature range may result in reduced long-term reliability ofthe x-ray target material, leading to higher direct costs associatedwith servicing the tube, and higher indirect costs for the user and alsoreduction in the range of operating current values if the system isrunning either above or below the optimal operating range.

A typical conditioning procedure may dump thermal energy into the x-raytube target, generally without consideration of the actual level ofenergy required to reach the optimal operating state. This can lead torestricted access to peak capability as the tube must cool downsufficiently from this excessively applied heat energy at the start ofthe actual diagnostic scan. For any CT-based procedure that involvesscanning patient anatomy, the level of patient absorbed dose to x-rayradiation is critical to the consideration of the appropriateness of theprocedure. During a scan or prior to it, appropriate measures may beundertaken to ensure that a radiation exposure of the patient does notexceed a pre-determined level.

One or more scout scans may be performed prior to a diagnostic scan. Ahigher power x-ray beam may be used during a scout scan to condition thex-ray tube for an immediately subsequent diagnostic scan.

Immediately prior to a scout scan, a targeted level of energy to reachthe desired x-ray target temperature range may be provided as an inputto a scan parameter optimizing algorithm. Further, a limit for radiationabsorbed dose of the patient may be used as an input to the scanparameter optimizing algorithm. The algorithm may then adjust the scanparameters for the subsequent scout scan such that the targeted energymay be imparted to the x-ray tube to optimally condition the tube forthe subsequent diagnostic scan while also exposing the patient to onlythe user-selected level of absorbed dose for the scout scan. By adding ahardening filter in the path of the x-ray beam reaching the subjectduring a scout scan, the beam reaching the subject may be attenuated,thereby reducing the radiation exposure of the subject. By using ahigher powered beam during a scout scan, the image quality of the scoutscan may be improved with key attributes of the scout mode also beingmaintained or improved, such as maintaining the ability to confidentlyprescribe a scan range for the subsequent diagnostic scan and maintainthe contrast to noise ratio of the underlying scout image.

FIG. 11 shows example method 1100 for using a scout scan forconditioning an x-ray tube prior to a diagnostic scan. Method 1100 maybe carried out after completion of a diagnostic scan and/or uponreceiving indication (such as via an operator) that a diagnostic scan isimminent.

At 1102, the routine includes determining if x-ray tube warmup isdesired prior to a scan. An x-ray tube warmup may include increasing thetemperature of the x-ray tube and the x-ray target to a desiredtemperature range. In one example, the desired temperature range may bebetween 200° C. and 300° C. An x-ray tube warm up may be desired priorto a diagnostic scan so that the target material reaches a desiredtemperature range. Below the desired temperature range, the targetmaterial may be brittle whereby a high-energy electron beam impinging onthe target may result in stress fractures such that a target degradationmight ensue. Use of a higher x-ray power during a scan may result in animproved image quality.

If it is determined that an x-ray tube warmup is not desired, at 1104,the current x-ray tube condition may be maintained. In one example, inthe current x-ray tube condition, x-rays may not be generated toactively heat the tube. In another example, x-ray generation in thex-ray tube may be continued without any alterations.

If it is determined that x-ray tube warmup is desired prior to a scan,at 1106, an allowable patient absorbed dose range may be received asinput from an operator. The upper limit of the allowable absorbed doserange may correspond to a level of x-ray exposure that may not have anydetrimental effect on the subject who is being scanned. As an example,an exposure level of an x-ray radiation coming in contact with thesubject may be given by equation 1.

$\begin{matrix}{{CTDI}_{Vol} = {\left( \frac{{Scout}\mspace{14mu}{Power}}{{Cradle}\mspace{14mu}{Power}} \right)*\left( {{CTDI}_{w}^{Ref}*{Aperture}} \right)}} & (1)\end{matrix}$

where CTD_(vol) is the upper limit of the user defined range ofallowable patient x-ray absorbed dose, CTDI_(w) ^(Ref) is the subjectabsorbed dose at a reference technique where CTDI_(w) ^(Ref) is based ona voltage (kV) in the x-ray tube, Scout power is a function of thevoltage (kV) in the x-ray tube and the current (mA) in the x-ray tube,Cradle speed is the speed in mm/second of the bed on which the subjectis positioned, and aperture is the beam aperture at system isocenter. Asan example, patient exposure to radiation may be the patient absorbeddose or the radiation during the scout scan (scout CTDIvol). The patientexposure may be different form that acquired by the CT system. At 1108,a number of scout scans to be performed prior to the diagnostic scan maybe determined. The operator may input the number of scout scans desiredvia a keyboard or a touchscreen in the operator console. As an example,two scout scans may be carried out, one from a side and another from thefront of a subject.

At 1110, a scan range for the scout scans may be determined. The timeduration of the scout scan may be determined by the combination of thescan range and the cradle speed. As an example, the cradle may be ableto move between a minimum speed and a maximum speed. The time durationof the scout scan may be a function of the cradle speed. The timeduration of the scout scan may be highest at the lowest cradle speed.Therefore, the scan range may also set a maximum time duration of thescout scan.

At 1112, an initial (current) temperature of the x-ray tube may bedetermined along with a desired x-ray target temperature at the onset ofthe subsequent diagnostic scan (referred herein as final temperature).In one example, a thermal model may be used to estimate the initialtemperature of the x-ray tube. The initial temperature may be moldedbased on ambient temperature, exposure history (such as power of x-raygenerated in the tube) over a last calibrated duration (such as overlast 5 hours), and thermal properties of the x-ray tube such as heattransfer coefficient of the tube and the target. The model may estimatea thermal state of the tube including a temperature of the target as thestate evolves over time. As such the temperature of the target may besame as the temperature of the tube and other associated components. Inanother example, the target temperature may be different from that ofthe tube and a separate initial target temperature and initial tubetemperature may be estimated. In another example, x-ray tube temperaturemay be estimated based on inputs from a temperature sensor housed in thex-ray tube.

The desired target temperature at the start of the scan and the timeremaining between the completion of the scout scan and the start of thediagnostic scan may be termed as the end criteria. The end criteria maybe built into some tools or system presets, or may be selected by theuser. As an example, a user may input or select the desired temperatureaccording to a scanning protocol or a menu. Also, the user may input thestart time of the upcoming diagnostic scan.

In one example, for patient scanning, the user and/or the system maydetermine that the tube target should be above 200° C. five minutesafter the completion of the scout scan. This may allow enough time toprepare the patient, position the anatomy and prepare for a contrastinjection, while ensuring the target is still above brittle mode toavoid cold tube limits and allow the maximum available tube power forpatient imaging. In another example, the user may want to extend thetime to 200° C. (at the onset of the scan) to 10 minutes after thecompletion of the scout scan during conditions when more time is neededfor a difficult patient or a procedure before the diagnostic exposure.

At 1114, an amount of energy to be imparted to the x-ray tube to attainthe desired x-ray target temperature may be estimated based on theinitial temperature and the desired x-ray target temperature at theonset of the subsequent diagnostic scan (final temperature). The desiredamount of energy may be estimated as a function of the initialtemperature, the final temperature, and a time duration between acompletion of the scout scan(s) and the onset of the diagnostic scan. Inone example, if two or more scout scans are successively carried out,the desired energy may be divided and imparted in two or moreinstallments. The energy imparted to an x-ray tube during a scout scanmay be given by equation 2.

$\begin{matrix}{{Energy} = {\left( \frac{{Scout}\mspace{14mu}{Power}}{{Cradle}\mspace{14mu}{Power}} \right)*{Scout}\mspace{14mu}{Length}}} & (2)\end{matrix}$

where energy is the amount of energy imparted to a x-ray tube during ascout scan, scout power is the mathematical product of the magnitudes ofx-ray tube voltage and x-ray tube current, cradle speed is the speed inmm/second of the bed on which the subject is positioned, scout length isthe total duration of the number of scout scans to be carried out. Thescout length may be a function of the number of scout scans to becarried out and the duration of each scout scan.

At 1116, the scan parameter optimizing algorithm may be used todetermine the scan parameters for the scout scan based on an allowablepatient absorbed dose range (as determined in step 1106), the number ofscout scans (as determined in step 1108), the scan range for each scoutscan (as determined in step 1110), and the desired energy for x-raytarget warm up (as determined in step 1114). The power to be provided tothe tube for attaining the desired final thermal state is a function ofthe desired energy for x-ray tube warm up and the duration of the scoutscan(s). The algorithm may estimate the power to be provided to the tubeover the course of the scan(s) and determines current and voltage of thex-ray tube corresponding to the power. As such, different power levelsprovide different dosage of x-ray.

The scan parameters prescribed by the scan parameter optimizingalgorithm based on the above mentioned inputs may include x-ray tubevoltage (kV), x-ray tube current (kA), cradle speed during the scan(mm/sec), beam aperture at system isocenter, beam focal point size, scanfield of view, the one or more filters to be used, etc. The scanparameter optimizing algorithm may automatically prescribe the scanparameters prior to the onset of the scout scan(s).

The scout scan parameters are tailored to match the energy demand of thesystem and patient absorbed dose limit as set by the user. To accomplishthis the algorithm automatically selects the above mentioned scanparameters in order to match the system thermal input demand,user-selected absorbed dose range, and the independently set scan range,and produce a scout scan that meets the input energy target, within thepatient absorbed dose range, over the course of the scan range. As anexample, energy targets may be in the range of 25-400 kJ over all validscout scan ranges 50-2000 mm. Acceptable (user set) patient absorbeddose levels may be in the range of 0.02 mGy-0.5 mGy. As an example, ifthe energy demand is 200 kJ, the scout scan range is independently setto 450 mm, and the user has chosen a scout CTDIvol range between0.02-0.06 mGy, the algorithm may automatically select an x-ray tubevoltage of 80 kV, an x-ray tube current of 555 mA, and a cradle speed of100 mm/sec., resulting in an imparted energy of 200 kJ at an absorbeddose of 0.04 mGy. This example illustrates the mechanism behind how thealgorithm chooses the system parameters to meet the dual targets ofimparted energy and patient absorbed dose.

FIG. 12 shows a block diagram 1200 illustrating a guided selection of ascan protocol. A scan parameter optimizing algorithm 1202 may be used todetermine scout scan parameters 1212. Inputs to the scan parameteroptimizing algorithm 1202 may include a desired energy 1204 forattaining an optimal x-ray target temperature, a maximum permissiblesubject radiation absorbed dose level (or range) 1206, a scan range perscout scan 1210 such as a time duration of each scan, and a number ofscout scans 1210 to be carried out for imparting the desired energy1204. Based on the input, the scan parameter optimizing algorithm 1202may optimize the power to be delivered during the course of each scoutscan to be able to impart the desired level of energy over the entireduration of the scans. As an example, the algorithm may use a look-uptable to determine the scout scan parameters 1212 as output based on thepower to be delivered during each scan. The scout scan parametersautomatically set by the algorithm 1202 may include x-ray tube voltage(kV), x-ray tube current (kA), cradle speed during the scan (mm/sec),beam aperture at system isocenter, beam focal point size, scan field ofview, the one or more filters to be used, etc.

Returning to FIG. 11, at 1118, scout scan(s) may be initiated based onthe scan parameters prescribed by the algorithm. Prior to generation ofthe x-ray beam for the scout scan, a bowtie filter and a hardeningfilter may be positioned in the path of the x-ray beam by operating amotor coupled to a carriage including the bowtie filter (such as bowtiefilter 320 in FIG. 3) and the hardening filter (such as hardening filter302 in FIG. 3). The carriage may be moved along a shaft in a planeperpendicular to the plane of the x-ray beam to position the bowtiefilter and the hardening filter in the beam. The controller may actuatethe motor to move the shaft and the carriage to the desired position.The hardening filter may intercept lower energy radiations toattenuating the beam, thereby decreasing the radiation exposure of thepatient during the scout scan. By using the hardening filter, a higherpowered x-ray beam may be used to heat the x-ray tube during the scoutscan while maintaining the absorbed dose level of the subject within theuser specified absorbed dose range. The hardening filter may at leastpartially overlap with the bowtie filter and the beam may first passthrough the hardening filter and then enter the bowtie filter. Once thefilters are positioned in the path of the beam, radiation source may beactivated to generate x-rays. The dataset of the scout scan is acquiredfrom the detector (such as 108 of FIG. 2) upon receiving the transmittedradiation signal from the imaging subject.

In this way, a carriage may include a hardening filter and one or morebowtie filters, and a filter driving system for moving the carriage toselectively position the hardening filter and one of the one or morebowtie filters in a path of a radiation beam between a radiation sourceand an imaging subject during a scout scan preceding a diagnostic scan,the scout scan carried out according to scan parameters computed basedon a selected patient radiation absorbed dose limit and an amount ofenergy to be imparted to a x-ray tube of the radiation source for x-raytube warmup.

At 1120, the routine includes determining if the scout scan has ended.The end of the scout scan may be determined based on the scan parametersdetermined by the algorithm at step 1116. If it is determined that thescout scan has not ended, at 1121, the scout scan may be continued toheat the x-ray tube. In one example, two or more scout scans may becarried out successively. The scan parameters for each scout scan may beprescribed by the algorithm.

If it is determined that the scout scan has ended, at 1122, the acquireddataset from the scout scan is displayed and stored. In one embodiment,dataset acquired from different sections of the subject may bere-constructed to form an image. The acquired dataset, as well as theprocessed images may be saved in the storage of the imaging system andno further scans may be carried out.

At 1122, x-ray generation may be initiated by activating the radiationsource and the diagnostic scan may commence according to the scanparameters set-up. A bowtie filter may be positioned in the path of thex-ray beam by operating a motor coupled to a carriage including thebowtie filter. The hardening filter may be moved out of the path of thex-ray beam and at least one bowtie filter may be positioned in the pathof the x-ray beam. The type of the filter may be determined based on theanatomy of the currently imaged section of the subject. For a diagnosticscan, a larger beam size is used and therefore a hardening filter may nolonger be used. In one example, the bowtie filter used for thediagnostic scan may be same as the bowtie filter used in the scout scan.In another example, the bowtie filter used for the diagnostic scan maybe different from the bowtie filter used in the scout scan. The carriagemay be moved along a shaft in a plane perpendicular to the plane of thex-ray beam to position the bowtie filter in the beam.

In this way, prior to initiation of a diagnostic scan, user input may bereceived for each of a patient absorbed dose limit, duration of one ormore scout scans preceding the diagnostic scan, a number of scout scans,a final temperature of an x-ray tube at the initiation of the diagnosticscan, an amount of energy to be imparted to a x-ray tube during the oneor more scout scans may be estimated based on a current temperature ofthe x-ray tube temperature, the final temperature of the x-ray tube, anda time of initiation of the diagnostic scan, scan parameters for the oneor more scout scans may be computed based on a patient absorbed doselimit and the amount of energy to be imparted to the x-ray tube duringthe one or more scout scans, a beam hardening filter may be positionedin a path of an x-ray beam, and the one or more scout scans may beperformed according to the computed scan parameters to warm-up the x-raytube.

FIG. 13 shows an example plot 1300 of variation in x-ray targettemperature during a scout scan and a subsequent diagnostic scan. Line1302 shows a variation in x-ray target temperature as estimated via athermal model or output of a temperature sensor housed in the x-raytube. For a diagnostic scan, the desired temperature range for thetarget is between temperature T2 and temperature T3.

A scout scan may be initiated at time t1. Prior to the scout scan, thetemperature of the target may be between temperature T1 and temperatureT2. If a diagnostic scan is carried out below temperature T2, the targetmaterial may be brittle whereby a high-energy electron beam impinging onthe target may result in stress fractures such that a target degradationmight ensue. During x-ray generating during a scout scan, at time t2,the temperature of the target may increase to above temperature T3.Carrying out a diagnostics scan above T3 may cause degradation of thex-ray tube.

By the time the diagnostics scan is carried out at time t3, thetemperature of target may decrease to the optimal temperature rangebetween T1 and T2 where the target material is ductile and ahigh-powered x-ray beam may be used for the diagnostic scan without anydetrimental effects to the tube. As an example, T1 may be 100° C., t2may be 200° C., and T3 may be 300° C.

In this way, the scan parameter optimizing algorithm may automaticallyprescribe several scan technique parameters (such as tube voltage,cradle speed, current, bowtie filter, x-ray beam aperture) of the scoutscan to concurrently impart a targeted level of thermal energy to thex-ray tube system, while exposing the patient to a user-selected x-rayabsorbed dose within a targeted absorbed dose range. This algorithmaccomplishes this dual task while improving the image quality of thescout scan during a procedure that is part of routine patient workflow.Optimal thermal conditions of the x-ray tube during a diagnostic scantranslates directly to increased reliability of the x-ray tube leadingto a concurrent reduction in commercial costs of replacement and anincrease in customer satisfaction.

By thermally conditioning the x-ray tube prior to a diagnostic scan,maximum power capability of the CT system may be used during scans andconsistency of diagnostic image quality will therefore be improved. Useof a scout scan for x-ray tube conditioning may reduce or negate theneed for separate and additional out of room tube warmups that occurduring a standard day of scanning workflow, sometimes as part of thepatient scanning schedule, where the timing needs to be managed by a CTtechnologist, thereby improving workflow.

FIGS. 1-5D, 7, and 8A-8B show example configurations with relativepositioning of the various components. If shown directly contacting eachother, or directly coupled, then such elements may be referred to asdirectly contacting or directly coupled, respectively, at least in oneexample. Similarly, elements shown contiguous or adjacent to one anothermay be contiguous or adjacent to each other, respectively, at least inone example. As an example, components laying in face-sharing contactwith each other may be referred to as in face-sharing contact. Asanother example, elements positioned apart from each other with only aspace there-between and no other components may be referred to as such,in at least one example. As yet another example, elements shownabove/below one another, at opposite sides to one another, or to theleft/right of one another may be referred to as such, relative to oneanother. Further, as shown in the figures, a topmost element or point ofelement may be referred to as a “top” of the component and a bottommostelement or point of the element may be referred to as a “bottom” of thecomponent, in at least one example. As used herein, top/bottom,upper/lower, above/below, may be relative to a vertical axis of thefigures and used to describe positioning of elements of the figuresrelative to one another. As such, elements shown above other elementsare positioned vertically above the other elements, in one example. Asyet another example, shapes of the elements depicted within the figuresmay be referred to as having those shapes (e.g., such as being circular,straight, planar, curved, rounded, chamfered, angled, or the like).Further, elements shown intersecting one another may be referred to asintersecting elements or intersecting one another, in at least oneexample. Further still, an element shown within another element or shownoutside of another element may be referred as such, in one example.

In one example, a method for an imaging system, comprises: prior to adiagnostic scan, generating x-ray in an x-ray tube of a radiation sourceto condition the x-ray tube that is adjusted based on an initialtemperature of the x-ray tube and a desired temperature of the x-raytube for the diagnostic scan. The preceding example method, additionallyor optionally, further comprising, via a closed loop control system,estimating an amount of energy to be delivered to the x-ray tube duringthe conditioning of the x-ray tube based on the initial temperature ofthe x-ray tube and an end criteria. In any or all of the precedingexamples, additionally or optionally, the initial temperature of thex-ray tube is estimated via a thermal model, the initial temperaturemodeled based on one or more of an ambient temperature, power of x-raygenerated in the x-ray tube over a last threshold duration, and thermalproperties of the x-ray tube. In any or all of the preceding examples,additionally or optionally, the end criteria includes the desiredtemperature of an x-ray tube at a start of the diagnostic scan and atime duration between an end of the conditioning of the x-ray tube andthe start of the diagnostic scan. In any or all of the precedingexamples, additionally or optionally, the desired temperature of thex-ray target at the start of the diagnostic scan is a function of afinal temperature of the x-ray tube at the end of the conditioning ofthe x-ray tube, the thermal properties of the x-ray tube, and the timeduration between the end of the conditioning of the x-ray tube and thestart of the diagnostic scan. In any or all of the preceding examples,additionally or optionally, adjusting the generated x-ray includes,during the conditioning of the x-ray tube, adjusting a power deliveredto the x-ray tube based on the estimated amount of energy. In any or allof the preceding examples, additionally or optionally, the power to bedelivered may be delivered during a single x-ray exposure or over aseries of sequential x-ray exposures during the conditioning of thex-ray tube. Any or all of the preceding examples, further comprising,additionally or optionally, during the generation of the x-ray,positioning a blocking plate in a path of an x-ray beam to block thex-ray beam from exiting a collimator. In any or all of the precedingexamples, additionally or optionally, the collimator receives the x-raybeam from a window in the x-ray tube via one or more filters. In any orall of the preceding examples, additionally or optionally, the blockingplate is positioned over an output port of the collimator completelyblocking an aperture and the output port of the collimator, the apertureformed by a gap between a first collimator blade and a second collimatorblade. In any or all of the preceding examples, additionally oroptionally, the blocking plate is coupled to a lower surface of one ofthe first collimator blade and the second collimator blade, the lowersurface proximal to the output port of the collimator. Any or all of thepreceding examples, additionally or optionally, further comprising, inresponse to the temperature of the x-ray tube increasing to the finaltemperature of the x-ray tube at the end of the conditioning of thex-ray tube, suspending generation of the x-rays until the diagnosticscan is initiated.

Another example method imaging system comprises: an x-ray collimatorincluding a first collimator blade and a second collimator bladeseparated by a gap, the gap forming an aperture of the collimator; and ablocking plate coupled to the first collimator blade, the blocking platepositioned in a path of an x-ray beam to block the x-ray beam fromexiting the collimator during x-ray generation to condition a x-ray tubeprior to a diagnostic scan. In the preceding example method,additionally or optionally, the conditioning of the x-ray tube includesincreasing a temperature of the x-ray tube to a higher temperatureimmediately prior to the diagnostic scan, the higher temperaturecorresponding to a ductile state of an x-ray target. In any or all ofthe preceding examples, additionally or optionally, the blocking plateis coupled to a base of the first collimator blade, the blocking plateextending beyond a first edge of the base of the first collimator blade,wherein the first edge is distal from the second collimator blade. Inany or all of the preceding examples, additionally or optionally, theblocking plate is in face sharing contact with the base of the firstcollimator blade. In any or all of the preceding examples, additionallyor optionally, the blocking plate is moved out of the path of the x-raybeam by moving the first collimator blade during the diagnostic scan.

In yet another example, a method for the imaging system, comprises:prior to initiation of a diagnostic scan, warming-up a x-ray tube bygenerating x-ray in the x-ray tube, adjusting a power of the generatedx-ray via a closed loop control of a temperature of the x-ray tube, andduring the warm-up of the x-ray tube, blocking a x-ray beam from exitinga collimator by positioning a blocking plate in a path of the x-raybeam. In the preceding example method, additionally or optionally, theclosed loop control of the temperature includes, estimating an initialtemperature of the x-ray tube, estimating an amount of energy to bedelivered to the x-ray tube to attain a final temperature of the x-raytube at the initiation of the diagnostic scan based on the initialtemperature, and adjusting the power of the generated x-ray based on theestimated energy to be delivered to the x-ray tube. In any or all of thepreceding examples, additionally or optionally, adjusting the power ofthe generated x-ray includes adjusting a voltage of the x-ray tube andthe current of the x-ray tube during the generation of the x-ray in thex-ray tube.

As used herein, an element or step recited in the singular and proceededwith the word “a” or “an” should be understood as not excluding pluralof said elements or steps, unless such exclusion is explicitly stated.Furthermore, references to “one embodiment” of the present invention arenot intended to be interpreted as excluding the existence of additionalembodiments that also incorporate the recited features. Moreover, unlessexplicitly stated to the contrary, embodiments “comprising,”“including,” or “having” an element or a plurality of elements having aparticular property may include additional such elements not having thatproperty. The terms “including” and “in which” are used as theplain-language equivalents of the respective terms “comprising” and“wherein.” Moreover, the terms “first,” “second,” and “third,” etc. areused merely as labels, and are not intended to impose numericalrequirements or a particular positional order on their objects.

This written description uses examples to disclose the invention,including the best mode, and also to enable a person of ordinary skillin the relevant art to practice the invention, including making andusing any devices or systems and performing any incorporated methods.The patentable scope of the invention is defined by the claims, and mayinclude other examples that occur to those of ordinary skill in the art.Such other examples are intended to be within the scope of the claims ifthey have structural elements that do not differ from the literallanguage of the claims, or if they include equivalent structuralelements with insubstantial differences from the literal languages ofthe claims.

The invention claimed is:
 1. A method for an imaging system, comprising:prior to a diagnostic scan, generating x-ray in an x-ray tube of aradiation source to condition the x-ray tube that is adjusted based onan initial temperature of the x-ray tube, a desired temperature of thex-ray tube for the diagnostic scan, and a predicted decrease intemperature in a time frame between an end of the conditioning and astart of the diagnostic scan, the predicted decrease estimated via athermal model of the x-ray tube.
 2. The method of claim 1, furthercomprising, via a closed loop control system, estimating an amount ofenergy to be delivered to the x-ray tube during the conditioning of thex-ray tube based on the initial temperature of the x-ray tube and an endcriteria.
 3. The method of claim 2, wherein the initial temperature ofthe x-ray tube is estimated via the thermal model, the initialtemperature modeled based on one or more of an ambient temperature,power of x-ray generated in the x-ray tube over a last thresholdduration, and thermal properties of the x-ray tube.
 4. The method ofclaim 3, wherein the end criteria includes the desired temperature ofthe x-ray tube at the start of the diagnostic scan, the time framebetween the end of the conditioning and the start of the diagnosticscan, and the predicted decrease in temperature.
 5. The method of claim4, wherein the desired temperature of the x-ray tube at the start of thediagnostic scan is a function of a final temperature of the x-ray tubeat the end of the conditioning of the x-ray tube, the thermal propertiesof the x-ray tube, and the time frame between the end of theconditioning of the x-ray tube and the start of the diagnostic scan. 6.The method of claim 2, wherein adjusting the generated x-ray includes,during the conditioning of the x-ray tube, adjusting a power deliveredto the x-ray tube based on the estimated amount of energy.
 7. The methodof claim 5, wherein the power to be delivered may be delivered during asingle x-ray exposure or over a series of sequential x-ray exposuresduring the conditioning of the x-ray tube.
 8. The method of claim 7,further comprising, during the generation of the x-ray, positioning ablocking plate in a path of an x-ray beam to block the x-ray beam fromexiting a collimator.
 9. The method of claim 8, wherein the collimatorreceives the x-ray beam from a window in the x-ray tube via one or morefilters.
 10. The method of claim 7, wherein the blocking plate ispositioned over an output port of the collimator completely blocking anaperture and the output port of the collimator, the aperture formed by agap between a first collimator blade and a second collimator blade. 11.The method of claim 10, wherein the blocking plate is coupled to a lowersurface of one of the first collimator blade and the second collimatorblade, the lower surface proximal to the output port of the collimator.12. The method of claim 1, further comprising, in response to thetemperature of the x-ray tube increasing to the final temperature of thex-ray tube at the end of the conditioning of the x-ray tube, suspendinggeneration of the x-rays until the diagnostic scan is initiated, thefinal temperature reached at the end of the conditioning being higherthan the desired temperature of the x-ray target at the start of thediagnostic scan.
 13. A method for an imaging system comprising: prior toinitiation of a diagnostic scan, warming-up an x-ray tube by generatingx-ray in the x-ray tube; adjusting a power of the generated x-ray, via aclosed loop control of a temperature of the x-ray tube, based on adesired temperature of the x-ray tube for the diagnostic scan and apredicted decrease in temperature in a time frame between an end ofwarmup and a start of the diagnostic scan as estimated via a thermalmodel of the x-ray tube; and during the warm-up of the x-ray tube,blocking a x-ray beam from exiting a collimator by positioning ablocking plate in a path of the x-ray beam.
 14. The method of claim 13,wherein the closed loop control of the temperature includes, estimatingan initial temperature of the x-ray tube, estimating an amount of energyto be delivered to the x-ray tube to attain a final temperature of thex-ray tube at the initiation of the diagnostic scan based on the initialtemperature and the predicted decrease in temperature in a time framebetween the end of warmup and the start of the diagnostic scan, andadjusting the power of the generated x-ray based on the estimated energyto be delivered to the x-ray tube, the final temperature of the x-raytube at the initiation of the diagnostic scan lower than an endtemperature at the end of the warm-up.
 15. The method of claim 13,wherein adjusting the power of the generated x-ray includes adjusting avoltage of the x-ray tube and a current of the x-ray tube during thegeneration of the x-ray in the x-ray tube.